Prosthesis socket and system comprising a prosthesis socket and prosthesis device

ABSTRACT

The invention relates to a prosthesis shaft for receiving an amputation stump of an extremity, comprising connecting means for a distal prosthesis device ( 2 ), wherein the prosthesis shaft ( 1 ) comprises at least one shell ( 11, 12 ), which has an arched, open cross-section and the shell ends of which in the applied state overlap each other at least partially, at least one tensioning means ( 14, 15 ) being disposed on the shell ( 11, 12 ), said means acting in the circumferential direction and tensioning the shell ends relative to each other, and the shell ( 11, 12 ) being made of a dimensionally stable plastic having regions with varying elasticity.

CROSS-REFERENCE TO RELATED APPLICATIONS

This application is a divisional application of U.S. patent applicationSer. No. 12/670,458, filed Jan. 25, 2010, now issued U.S. Pat. No.8,906,112.

FIELD OF THE INVENTION

The invention relates to a prosthesis socket for receiving an amputationstump of an extremity, with connecting means for a distal prosthesisdevice, and a system comprising a prosthesis socket and a prosthesisdevice.

BACKGROUND

The prior art discloses various methods and concepts by which patientswho have undergone amputations, e.g. of the lower extremities, arefitted with a prosthesis. In patients whose legs have been amputatedabove or below the knee or through the knee joint, a classical methodfor producing a prosthesis socket is the plaster cast method, in which aplaster cast is made of a patient's amputation stump and serves as atemplate for a stump model, and a prosthesis socket, for example a thighsocket, is formed on this stump model. This thigh socket is made from aplastic and completely surrounds the amputation stump.

Various concepts have been proposed for securing the thigh socket to thestump. For example, a liner is pulled over the amputation stump andbears sealingly on the outside on the socket. The air is removed fromthe space between the liner and the outer socket by way of a releasevalve or a pump, such that the prosthesis socket is held on theamputation stump of the patient by means of underpressure. In the caseof a release valve, the air taken is released at each step, and activeevacuation does not take place. In the case of a pin solution, the endof the liner is provided with a projection that is locked in the socket.Further prosthesis devices are then arranged on the prosthesis socketitself, for example prosthetic knee joints and additional devices suchas a connecting element and prosthetic foot.

Adapting prosthesis socket individually to the amputation stump isextremely difficult and time-consuming and has to be done by a trainedorthopedic technician. Several fittings are needed in order toindividually adapt the prosthesis socket, with the result that nine totwelve months may pass between the operation and the final provision ofan adapted prosthesis socket. These prosthesis sockets ensure a highdegree of stability and activity of the prosthesis user. Patients withan amputation of an upper extremity are treated in a comparable manner.

However, the patients who are to be provided with prosthesis devices donot all have the same requirement for extensive mobility. For example,elderly subjects who are suffering from diabetes, and who have had tohave parts of the lower extremities amputated on account of gangreneinduced by diabetes, are often unable to walk long distances. Inaddition, there are considerable fluctuations in the volume of theamputation stump, such that a correct adaptation of the prosthesissocket to the stump is possible only with difficulty. Moreover, thepatient is often unable to cooperate actively in the adaptation of theprosthesis socket. However, it is particularly important for these verypatients to be fitted with a prosthesis as soon as possible in order tobe able to minimize the period of confinement to bed. When treating theupper extremities, it is also important to adapt a prosthesis as quicklyas possible in order to ensure that motor capacity is not lost.

EP 1 656 911 A1 describes a prosthesis socket with a closed shell andwith an element which is arranged laterally therein and which is pulledin the direction of the stump via a tensioning strap that is guided intothe shell through two slits. The bottom of the shell is padded and hasconnecting means for a lower leg.

DE 32 29 812 A1 relates to a stump-receiving shell for an artificiallimb, with at least one shell which has a curved, open cross section andof which the ends at least partially overlap each other in the statewhen applied. Tensioning means arranged on the shell act in thecircumferential direction and clamp the shell ends on each other.

SUMMARY

The object of the present invention is to make available, particularlyfor geriatric patients, a prosthesis socket and a system composed of aprosthesis socket and of prosthesis devices secured thereon, permittingrapid adaptation to the patient and inexpensive fitting, such that thepatient remains active or is mobile again as soon as possible.

In the prosthesis socket according to the invention for receiving anamputation stump of an extremity, with connecting means for a distalprosthesis device, the prosthesis socket comprises at least one shell,which has a curved, open cross section and of which the shell ends, inthe applied state, at least partially overlap each other, and at leastone tensioning means is arranged on the shell and is active in thecircumferential direction. The tensioning means permits rapid and easyadaptation of the prosthesis socket, in particular the thigh socket, tothe contour of the amputation stump, since the tensioning can bringabout a radial shifting of the shell ends toward each other, with theresult that it is no longer necessary to take individual impressions. Byprovision of the tensioning means, the prosthesis socket, and thereforethe entire prosthesis, can also be applied and taken off again quicklyand easily, thereby increasing the acceptance of the prosthesis by theprosthesis user. In this way, patients who have only recently undergonesurgery can be quickly fitted with a prosthesis, with the result thatthe period of reduced mobility or activity is reduced. The shell can bespiral-shaped, for example, allowing the circumference of the socket tobe modified via the one or more tensioning means. Likewise, two mutuallyopposite shell areas can overlap each other such that, when theeffective length of the one or more tensioning means is changed, afolding overlapping movement takes place instead of a rotatingoverlapping movement. The shell can be configured in one piece. Theshell or partial shells are preferably produced from a dimensionallystable plastic in order to allow the prosthesis socket to be made aslight as possible. The shell or partial shells have areas of differentelasticity in order, on the one hand, to satisfy the stabilityrequirements and, on the other hand, to ensure comfort during use. Thus,the shell or partial shells are made flexible in the proximal area forexample, particularly in the frontal and dorsal directions, such thatthe patient does not find it uncomfortable to be sitting down with theprosthesis applied. The areas of different flexibility can be obtainedby using materials having different physical properties or by usingdifferent thicknesses of material. The more flexible areas are generallythinner than the stiffer areas or can be made from a more flexiblematerial than the rest of the shell, for example by two-componentinjection molding.

The shell can be made up of several partial shells, which are designedto be able to move relative to one another. Two or more partial shellscan be combined to make one overall shell in which the partial shellsare arranged like leaves at least partially overlapping each other. Thepartial shells can also be connected to one another or formed integrallyon one another in their distal areas, such that an elastic bearing forseveral shell-like parts is formed at one common area.

The shell or partial shells are preferably arranged medially andlaterally on the amputation stump and each have at least one connectingmeans for the distally adjoining prosthesis device. The medial/lateralarrangement makes it possible for the overlapping of the shell ends orpartial shells to be arranged at the front and rear, in order to achieveincreased stability there. With this arrangement, the connecting meansfor securing the prosthesis device can also be provided medially andlaterally. In an alternative embodiment, there is a unilateralattachment permitting either a medial or lateral arrangement of theconnecting means, thereby increasing the range of configurations of theprosthesis. In this way, individual preferences or needs can be moreeasily taken into consideration.

The shell or partial shells are medially and laterally stiff and have ahigh degree of resistance to deformation, particularly against bendingabout an axis in the forward direction or direction of walking, so as tobe able to provide sufficient stability. The stiffness is supported by acurvature of the shell or partial shells. The shell or shells can alsobe attached to the frame on one side. This unilateral attachment caneither be on the medial or lateral side.

Easier adaptation and overlapping of the shell or partial shells ispermitted by providing them with a curvature, such that they can bepushed or plugged into each other. In this case, one partial shell has agreater radius of curvature than the other partial shell, such that onepartial shell can be overlapped on the outside by the other at bothends. It is also possible to perform an approximate preliminary shapingto the form of the stump.

The connecting means for securing the distal prosthesis device arepreferably arranged in the proximal, stiff area of the shell or partialshells. Particularly in the case of above-knee amputations, theconnecting means are positioned in the area of the greater trochanter.In a development of the invention, the center of rotation of theconnecting means is arranged in the area of the greater trochanter,while the connecting means themselves are secured on another part of theshell or of the partial shells. For example, the rotation point can bemoved in the direction of the greater trochanter via suitably curvedguides.

The connecting means can be arranged or designed for the pivotablebearing of the prosthesis device, the pivotability being provided onlyfor a small angle range in order to facilitate the prosthesis setup,that is to say the orientation of the prosthesis elements with respectto one another and to the body. After the prosthesis setup has beenfinalized, the prosthesis device can be fixed in the correct positionvia fixing devices, for example screws or pins. The fixing device can beguided in an oblong hole, for example in a curved oblong hole, in orderto facilitate the prosthesis setup.

In principle, the shell or partial shells, in the applied state or whenconnected to each other, form an opening both at the proximal end andalso at the distal end. In order to close this opening, a cap issecured, in particular releasably secured, as a distal closure piece onthe shell or at least a partial shell, in order to protect distal end ofthe amputation stump.

In order to facilitate the insertion of the amputation stump providedwith a liner and also to ensure a stable relationship between amputationstump and prosthesis socket, the inner face of the shell or partialshells is provided or coated with a direction-dependent surfaceconfiguration, e.g. a nap velour, which has an orientation permittingeasy insertion but offering increased resistance counter to thedirection of insertion. The surface configurations, e.g. fibers, are forthis purpose inclined in the distal direction, while the outer face ofthe liner has a configuration or coating in an oppositely directed napor is provided with a surface suitably interacting with the surfaceconfiguration or the velour. The design of the socket and of the linerwith direction-dependent surface configurations can also be usedindependently of the construction of the socket in other designs of thesocket and represents an independent solution to the problem of holdinga liner in a socket.

Alternatively or in addition to this, the inner face of the partialshells is coated with an adhesive layer, for example of silicone,polyurethane or a copolymer, or if appropriate provided only in someareas with an adhesive coating, in order to ensure better adherence to aliner that is provided with a corresponding outer coating.

The tensioning means provided can be velcro tapes, ski-boot fasteners,clips or straps, and alternative securing means can also be provided forthe variable adjustment of the circumference of the shell or of thespacings or overlaps of the partial shells and for securing the partialshells or the ends of the shells to each other. The tensioning means arepreferably arranged and guided on the outer face of the socket, in orderto avoid direct contact with the stump and thus avoid the danger of thestump becoming caught.

The tensioning means can be guided across the front. In particular, theclosure devices or levers are arranged at the front in order to make theprosthesis and the prosthesis socket easy to apply and to take off. Theone or more tensioning means preferably act in circular configuration.

For individual adaptation of the shell or partial shells to the stumpcontour, at least two tensioning means are axially offset relative toeach other on the prosthesis socket, as a result of which a cone isformed that widens in the proximal direction. The fluctuations involume, which can differ in degree along the length of the amputationstump, can also be better compensated for when several tensioning meansare used. The tensioning means can also be arranged with two axiallyoffset guides.

The prosthesis device to be secured on the prosthesis socket comprises aframe which is secured preferably laterally and/or medially on theprosthesis socket, the frame preferably being designed as an outerframe, which is produced from a metal profile, for example. Securing onone side may be sufficient, in which case medial securing is preferablychosen. The further prosthesis devices, for example a prosthetic kneejoint or the like, can then be secured on the frame. The prosthesissocket and the prosthesis device, which can in each case be differentlydesigned depending on the height of the amputation, form a system forfitting a patient with a prosthesis.

BRIEF DESCRIPTION OF THE DRAWINGS

Illustrative embodiments of the invention are explained in more detailbelow with reference to the attached figures, in which:

FIG. 1 shows a system comprising prosthesis socket and prosthesisdevice, in the state when applied;

FIG. 2 shows a separate view of the prosthesis socket and of aprosthesis device secured thereon;

FIG. 3 shows a detail of an assembled prosthesis socket;

FIG. 4 shows a prosthesis socket with separate partial shells;

FIG. 5 shows a prosthesis socket in an exploded view;

FIG. 6 shows a detail of a partial shell with fitted frame;

FIG. 7 shows a side view of a fitted partial shell;

FIG. 8 shows a pivoted partial shell;

FIG. 9 shows an alternative embodiment of the socket in an openposition; and

FIG. 10 shows a prosthesis socket according to FIG. 9 in a closedposition.

DETAILED DESCRIPTION

In FIG. 1, a system comprising a prosthesis socket 1, here a thighsocket, and a prosthesis device 2 secured thereon is shown in a statewhen applied, along with a schematic depiction of the healthy right leg.In this illustrative embodiment, the prosthesis socket 1 is composed oftwo partial shells 11, 12 which are arranged around the amputation stumpand overlap each other. The prosthesis socket 1 is adapted to thecircumference and the contour of the amputation stump via two tensioningmeans 14, 15 that are secured and axially offset from each other on thepartial shells 11, 12. Arranged between the prosthesis socket 1 and theamputation stump there is a liner (not shown), which is pulled over theamputation stump and completely avoids direct contact of the partialshells 11, 12 with the skin of the amputation stump. A mechanicalcoupling between the prosthesis socket 1 and the amputation stump isproduced by the liner.

The two partial shells 11, 12 are produced from a planar, dimensionallystable plastic and have a curvature, such that they bear with thegreatest possible surface area on the prosthesis socket or the liner. Inthe embodiment shown, the medial partial shell 12 is overlapped on theoutside by the lateral partial shell 11 in the frontal area. Acorresponding overlap can also take place in the dorsal area, whichmeans that the radius of curvature of the lateral partial shell 11 isgreater than that of the medial partial shell 12. The separate partialshells 11, 12 have an open cross section and, in the applied state, forma multi-part sleeve that is open at the proximal and distal ends. Thedistal end of the prosthesis socket 1 is here closed by a cap 13, whichis secured on the partial shells 11, 12. The cap 13 serves to protectthe distal end of the amputation stump. In principle, it is alsopossible for this cap 13 to be secured or formed on the liner.

In the proximal area of the prosthesis socket 1, the partial shells 11,12 are provided with connecting means 16 for securing a frame 20.Although the connecting means 16, which are designed as a screwconnection, are shown only on the lateral side, they are in fact presenton both partial shells 11, 12. The frame 20 is formed as a U-shapedbracket from a metal or plastic profile and serves as an outer frame, inorder to place the least possible strain on the prosthesis wearer. Thetwo arms of the U-shaped outer frame 20 are arranged medially andlaterally.

The frame 20 is adjoined distally by further components of theprosthesis device 20, in this case a prosthetic knee joint 21, aconnection element 22 and a prosthetic foot 23. The prosthesis device 2as a whole is preferably designed as a lockable knee joint or ahigh-stability knee joint, which has a simple construction and above allavoids any undesired bending-in of the prosthetic knee joint 21. Wherethe system is not used for the management of geriatric patients, butinstead as a form of primary treatment, other constructions of theprosthetic knee joint 21 can also be provided.

The system comprising prosthesis socket 1 and prosthesis device 2 isshown separately in FIG. 2. In contrast to FIG. 1, the medial partialshell 12 is here arranged on the outside and overlaps the lateralpartial shell 11. The tensioning means 14, 15, which can be designed asstraps, velcro tapes or, for example, ski-boot fasteners, can either besecured on just one partial shell 11, 12 and act in the circumferentialdirection, such that the partial shells 11, 12 are moved toward eachother, or they can establish the connection between the two partialshells 11, 12, such that one end point of a tensioning means 14, 15 isarranged on the medial partial shell 12 and a second end point isarranged on the lateral partial shell 11.

Since the system comprising prosthesis socket 1 and prosthesis device 2appears particularly suitable for less active patients who arefrequently seated, pressure sores can be avoided, and comfort enhanced,if the prosthesis socket 1 is soft and flexible in the frontal anddorsal areas, particularly in the proximal area of the partial shells11, 12, while the distal area of the partial shells 11, 12 is stable,particularly on the medial and lateral sides. The area of the connectingmeans 16 in particular is stable, such that the forces that occur duringwalking or standing can be introduced into the prosthesis socket 1. Theconnecting means 16 are secured as far as possible in the proximaldirection on the partial shells 11, 12, preferably in the area of thegreater trochanter when the prosthesis socket 1 is designed as a thighsocket.

FIG. 3 shows an enlarged detail of the prosthesis socket 1 with the twopartial shells 11, 12 and the tensioning means 14, 15 which, viainterlocking devices, are designed to adjust the circumference of theprosthesis socket 1. The preshaped partial shells 11, 12 have asufficient degree of flexibility, and at the same time stability, toprovide sufficiently exact adaptation to the amputation stump when thetightness of the tensioning means 14, 15 is altered. The outer frame 20with the brackets is secured medially and laterally, in particular by ascrew connection.

FIG. 4 shows the prosthesis socket 1 when opened. It will be noted thatthe medial partial shell 12 is received in the lateral partial shell 11and is overlapped by the latter to the front and back. In the proximalareas 110, 120 of the partial shells 11, 12, zones of lesser strengthand increased flexibility are formed, which make sitting easier. Thewall thickness in these areas 110, 120 can also be reduced in order tomake sitting easier when the prosthesis is applied. The tensioning means14, 15 are shown in the opened state. By opening up the tensioning means14, 15, it is possible to open the prosthesis socket 1 such that theprosthesis wearer can very easily apply the prosthesis socket 1 byclimbing into the opened prosthesis socket 1, pushing the partial shells11, 12 into each other and, when necessary, closing the tensioning means14, 15. By virtue of the variable configuration of the tensioning means14, 15, it is possible to take account of changes in the volume of theamputation stump and at all times to ensure a sufficiently securefastening of the prosthesis socket 1 to the amputation stump,particularly to the liner.

FIG. 5 shows the prosthesis socket 1 in an exploded view. The lateralpartial shell 11 is designed such that it covers the greater trochanter,while the medial partial shell 12 is designed such that the ischium isnot covered or only comes into contact with the flexible area 120. Thecap 13 is secured to the distal ends of the partial shells 11, 12 viasecuring tapes 18, for example velcro tapes. The securing tapes 18 arearranged crosswise and hold the cap 13 on the prosthesis socket 1, theopen edge of the cap 13 forming elastic fingers.

The inner faces 111, 121 of the partial shells 11, 12 can be providedwith various coatings in order to permit adherence to the liner orcoupling between liner and partial shells 11, 12. The coating 111, 121can be designed, for example, as a nap velour or as another fabric witha suitable orientation of the fibers, making it easier to insert theliner and the amputation stump into the substantially tube-shapedprosthesis socket 1 and at the same time preventing them from slippingout. For this purpose, the fibers or hooks can be inclined in thedirection of the distal edge, such that a movement of insertion is madeeasier, whereas a movement in the opposite direction is blocked or madedifficult. To release the socket 1 from the liner, the tensioning means14, 15 are opened up, and the prosthesis socket 1 is removed togetherwith the prosthesis device 2. It is also possible to coat the inner faceof the partial shells 11, 12 with a copolymer or silicone in order tosupport the adherence of the liner, which is provided on the outsidewith a corresponding coating.

FIG. 5 also shows the cuter frame 20, of which the proximal end hasbores 25 through which the connecting means 16 in the form of screws orpins are guided. Curved oblong holes 24 are also formed in the frame 20and receive means for fixing the prosthesis socket 1 relative to theframe 20.

FIG. 6 shows such an embodiment in the assembled state. The lateralpartial shell 11 is in this case secured on the frame 20 via a screw-inpin 16 as the connecting means. Another screw 26 is also guided in thecurved oblong hole 24 and protrudes through the oblong hole 24 and isscrewed into the lateral partial shell 11. Suitable threads can beworked and laminated into the plastic of the partial shell 11 in orderto permit stable securing of the frame 20 to the partial shell 11.

FIG. 7 shows a side view of the state according to FIG. 6. FIG. 8 showsthat the prosthesis socket 1, here the partial shell 11, is pivotablerelative to the frame 20 about the connecting means 15 in the form of ascrew, this pivoting being indicated by the double arrow. The screw 26slides to and fro inside the oblong hole 24 until an optimal orientationof the prosthesis socket with respect to the frame 20 is found. Thescrew 26 is then tightened and the thigh socket 1 is fixed relative tothe frame 20. This kind of adjustability is necessary since the hipmuscles tend to shorten when no extension takes place. When the subjectis for the most part in a seated position, the groin muscles contract,and the same is true when a counter-weight is absent on account of theamputation. The pivotability and adjustability are advantageous in termsof compensating for this flexion and providing a correct prosthesissetup.

The system of prosthesis socket 1 and prosthesis device 2 makes sittingcomfortable, and the prosthesis is also easy to apply and take off.Adaptation to a varying stump volume is easy, and there is no need forlengthy trial fittings or for taking impressions of the patient's stump.The joint device 21, for example, can make sitting down and standing upeasier, since various locking modes and damping stages can be set. It isalso possible to design the prosthetic joint 21 as a lockable kneejoint. In addition to its use in the management of geriatric patients,the system can also be used for rapid primary treatment, such thatpatients experience a period of immobility that is as short as possible.By virtue of the simple adaptation, it is easy to make adjustments tothe stump volume, which adjustments may be reversed on account of thehealing process. The adjustment is done by moving the separate partialshells 11, 12 relative to each other, so as to be able to allow for thechanging circumferences of the amputation stump.

FIG. 9 shows a perspective view of an alternative embodiment of theinvention with a one-part shell 10, which has an open cross section andis shown in an opened state. The opening is oriented to the front here,such that the prosthesis socket 1 can be easily applied by opening upthe prosthesis socket 10 and placing the stump, provided with a liner,into the opened prosthesis socket or into the opened shell 10. For thispurpose, the shell ends can be drawn apart from each other and caneasily curve outward, so as to permit simple insertion. The shell endsare then placed over each other, with the left-hand shell end in thiscase being placed under the right-hand, lateral shell end, such that anoverlap is obtained at the front. The tensioning means 14 is then guidedthrough a loop, for example, and turned back to permit securing. Thesecuring can be achieved by velcro closures or so-called ski-bootfasteners.

It will be seen from FIG. 9 that the distal end of the shell 10 is open,such that it is easy to adapt to different stump lengths, withoutadversely affecting the securing of the shell 10 at the correct site.

In FIG. 10, the illustrative embodiment according to FIG. 9 is shown ina closed state in which the left-hand shell end is placed underneath theright-hand shell end. The tensioning means 14 is secured in a zigzagformation on the shell 10 of the prosthesis socket and guided in aneyelet at the turning points. The tensioning means 14 can be secured onthe outer surface of the shell 10 by velcro closures, or an alternativesecuring means can also be provided. Tightening can take place via atoggle mechanism arranged at one end or via a ski-boot fastener. It willalso be seen from FIG. 10 that the distal end of the prosthesis socketis open, and the end can also be closed off or delimited by a closurecap. The shell 10 has a spiral-shaped arrangement such that, when thecircumference is adjusted, the shell ends slide in a spiral formationaround each other or the right-hand end of the shell 10 slides over theinner, left-hand end of the shell.

The invention claimed is:
 1. A prosthesis socket for receiving an amputation stump of an extremity, comprising: at least one shell with a curved, open cross section and ends which at least partially overlap each other in an applied state; at least one tensioning means arranged on the at least one shell, the at least one tensioning means being configured to act in a circumferential direction to tension the ends of the at least one shell relative to each other; and at least one connector associated with the at least one shell for connecting a distal prosthesis device, wherein the at least one shell is made from a dimensionally stable plastic with areas of different elasticity, and wherein an inner face of the at least one shell has a direction-dependent surface configuration that offers greater resistance to sliding counter to a direction of insertion of the amputation stump than sliding in the direction of insertion, wherein the direction of insertion is in a direction from a proximal edge of the at least one shell toward a distal edge of the at least one shell.
 2. The prosthesis socket as claimed in claim 1, wherein the at least one shell is made of several partial shells.
 3. The prosthesis socket as claimed in claim 1, wherein the at least one shell comprises at least two shells arranged medially and laterally with respect to the amputation stump.
 4. The prosthesis socket as claimed in claim 1, wherein the at least one shell is flexible in at least one proximal area of the at least one shell.
 5. The prosthesis socket as claimed in claim 1, wherein the at least one shell is stiff in medial and lateral directions.
 6. The prosthesis socket as claimed in claim 1, wherein the at least one shell is provided with a curvature configured to fit about a longitudinal extent of the amputation stump.
 7. The prosthesis socket as claimed in claim 1, wherein the at least one shell is preshaped for adaptation to the amputation stump.
 8. The prosthesis socket as claimed in claim 1, wherein the at least one connector is arranged in a proximal, relatively stiff area of the at least one shell.
 9. The prosthesis socket as claimed in claim 1, wherein the at least one connector is arranged on the at least one shell in an area of the at least one shell which corresponds in the applied state to a patient's greater trochanter.
 10. The prosthesis socket as claimed in claim 1, wherein the at least one connector permits rotation of the distal prosthesis device relative to the at least one shell, wherein a center of rotation of the at least one connector is arranged on the at least one shell in an area of the at least one shell which corresponds in the applied state to a patient's greater trochanter.
 11. The prosthesis socket as claimed in claim 1, further comprising one or more fixing devices for orienting the distal prosthesis device relative to the at least one shell, wherein the at least one connector is configured for a pivotable bearing of the distal prosthesis device.
 12. The prosthesis socket as claimed in claim 11, wherein the one or more fixing devices is guided in an oblong hole.
 13. The prosthesis socket as claimed in claim 12, wherein the oblong hole is curved.
 14. The prosthesis socket as claimed in claim 1, further comprising a cap secured as a distal closure piece on the at least one shell.
 15. The prosthesis socket as claimed in claim 14, wherein the cap is secured releasably on the at least one shell.
 16. The prosthesis socket as claimed in claim 1, wherein the direction-dependent surface configuration of the inner face of the at least one shell is a nap velour which is oriented in a distal direction of the at least one shell.
 17. The prosthesis socket as claimed in claim 1, wherein one or more inner faces of the at least one shell are coated with an adhesive layer.
 18. The prosthesis socket as claimed in claim 1, wherein the at least one tensioning means is selected from a group consisting of velcro tapes, ski-boot fasteners, clips, and straps.
 19. The prosthesis socket as claimed in claim 1, wherein the at least one tensioning means is positioned on a front portion of the prosthesis socket.
 20. The prosthesis socket as claimed in claim 1, wherein the at least one tensioning means includes two tensioning means that are axially offset on the at least one shell.
 21. The prosthesis socket as claimed in claim 1, wherein the at least one tensioning means is configured to act in a circular configuration.
 22. The prosthesis socket as claimed in claim 1, wherein the at least one tensioning means is arranged on the at least one shell with two axially offset guides.
 23. The prosthesis socket as claimed in claim 1, wherein the at least one shell forms a cone that widens in a proximal direction.
 24. The prosthesis socket as claimed in claim 1, further comprising a frame secured laterally, medially, or both laterally and medially on the at least one connector.
 25. The prosthesis socket as claimed in claim 24, wherein the frame is configured as an outer frame.
 26. The prosthesis socket as claimed in claim 24, wherein the frame is produced from a metal profile.
 27. The prosthesis socket as claimed in claim 24, further comprising a joint device secured on the frame.
 28. A prosthesis system, comprising: a prosthesis socket for receiving an amputation stump of an extremity, including: at least one shell with a curved, open cross section and ends which at least partially overlap each other in an applied state; at least one tensioning means arranged on the at least one shell, the at least one tensioning means being configured to act in a circumferential direction to tension the ends of the at least one shell relative to each other; and at least one connector associated with the at least one shell for connecting a distal prosthesis device, wherein the at least one shell is made from a dimensionally stable plastic with areas of different elasticity, and wherein an inner face of the at least one shell has a direction-dependent surface configuration that offers greater resistance to sliding counter to a direction of insertion of the amputation stump than sliding in the direction of insertion, wherein the direction of insertion is in a direction from a proximal edge of the at least one shell toward a distal edge of the at least one shell; and a prosthesis device secured to the at least one connector. 